Precision electrode movement control for renal nerve ablation

ABSTRACT

A catheter is configured to access a renal artery. A lumen of the catheter&#39;s shaft is dimensioned to receive a flexible actuation member which extends between the shaft&#39;s proximal and distal ends. The actuation member is moveable within the lumen and subject to elastic deformation, friction, and/or whip along its length. A flexible support member is coupled to a distal end of the actuation member and extendible beyond a distal tip of the shaft. An RF ablation electrode at a distal end of the support member is configured to ablated perivascular renal nerve tissue. A position converter at the distal end of the shaft is configured to convert movement of the actuation member into one or both of controlled rotational and axial movement of the support member and electrode to one of a multiplicity of stable circumferential positions substantially free of elastic deformation, friction, and/or whip impacting actuation member movement.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. Application Serial No. 13/194,920, filed Jul. 30, 2011, now U.S. Pat. No. 9,358,365, which claims the benefit of Provisional Patent Application Serial No. 61/369,463 filed Jul. 30, 2010, to which priority is claimed pursuant to 35 U.S.C. § 119(e) and which is hereby incorporated herein by reference.

SUMMARY

Embodiments of the disclosure are directed to control mechanisms situated at a distal end of an elongated flexible member that provide for precision movement of a component coupled to a distal end or other portion of the control mechanism. Embodiments of the disclosure are directed to control mechanisms situated at a distal end of an elongated flexible member dimensioned for deployment within a vessel of the body that provide for precision movement of a component coupled to a distal end or other portion of the control mechanism. Various embodiments are directed to a position converter situated at a distal end of a catheter and configured to convert movement of a proximal actuation member into one or both of controlled rotational movement and controlled axial movement of a component coupled to a distal end of the position converter substantially free of one or more of elastic deformation, friction, and whip impacting actuation member movement. Various embodiments are directed to a position converter situated at a distal end of a catheter and configured to convert movement of a proximal actuation member into one or both of controlled rotational movement and controlled axial movement of a component coupled to a distal end of the position converter to one of a plurality of stable circumferential and/or axial positions.

The position converter may comprise various types of orientation, positioning, and/or indexing components. For example, in some embodiments, the position converter may comprise a ratcheting arrangement configured to convert axial movement of a proximal actuation member into one or both of controlled rotational movement and controlled axial movement of a component coupled to the distal end of the position converter. In other embodiments, the position converter may comprise a magnetic indexing arrangement configured to magnetically urge a component coupled to the distal end of the position converter to one of a plurality of stable circumferential and/or axial positions. In further embodiments, the position converter may comprise a geometric keyed orientation mechanism configured to guide a key component of a proximal actuation member into and along a keyway arrangement that limits movement of a component coupled to the distal end of the position converter to one of a plurality of stable circumferential positions and/or stable axial positions. The component coupled to the distal end of the position converter may comprise a medical device, such as a sensor, an electrode, an ablation device, or other medical instrument. The component may comprise, for example, an ablation electrode or other type of ablation device, such as an ultrasound, laser, microwave, or thermal ablation device, configured for one or both of ablation and monitoring/imaging.

Embodiments of the disclosure are generally directed to apparatuses and methods for ablating target tissue of the body from within a vessel. Embodiments are directed to high frequency AC ablation catheters, systems, and methods that employ a control mechanism for moving an electrode during ablation with precision. Various embodiments of the disclosure are directed to apparatuses and methods for ablating perivascular renal nerves, such as for the treatment of hypertension.

According to various embodiments, an apparatus includes a catheter comprising a flexible shaft having a proximal end, a distal end, a length, and a lumen extending between the proximal and distal ends. The length of the shaft is sufficient to access a location within the body at or proximate target tissue to be ablated. A flexible actuation member is provided within the lumen of the shaft and extends between the shaft's proximal and distal ends. The actuation member is moveable within the lumen of the shaft and subject to one or more of elastic deformation, friction, and whip along its length during movement within the shaft's lumen. A flexible support is coupled to a distal end of the actuation member and extendible beyond a distal tip of the shaft. An electrode is provided at a distal end of the support member and configured to contact tissue at or near the target tissue.

The electrode is configured to deliver high frequency AC energy sufficient to ablate the target tissue proximate the electrode. The support member is configured to maintain a desired position of the electrode. A position converter is provided at the distal end of the shaft and configured to convert movement of the actuation member into at least controlled rotational movement of the support member and the electrode to one of a plurality of stable circumferential positions substantially free of the one or more of elastic deformation, friction, and whip impacting actuation member movement. In some embodiments, the position converter is configured to convert axial movement of the actuation member, which is subject to elastic deformation, friction, and whip, into controlled axial movement of the support member and the electrode to one of a plurality of stable axial positions.

In accordance with various embodiments, a catheter includes a flexible shaft having a proximal end, a distal end, a length, and a lumen extending between the proximal and distal ends. The length of the shaft is sufficient to access a patient's renal artery relative to a percutaneous access location. A flexible actuation member is provided within the lumen and extends between the proximal and distal ends of the shaft. The actuation member is moveable within the lumen of the shaft and subject to one or more of elastic deformation, friction, and whip along its length during movement within the shaft's lumen. A flexible support is provided at a distal end of the actuation member and extendible beyond a distal tip of the shaft and into a lumen of the renal artery. An electrode is provided at a distal end of the support member and configured to contact an inner wall of the renal artery and deliver high frequency AC energy sufficient to ablate perivascular renal nerve tissue proximate the electrode. The support member is configured to urge the electrode into contact with the inner wall of the renal artery.

A position converter is provided at the distal end of the shaft and configured to convert movement of the actuation member into at least controlled rotational movement of the support member and the electrode to one of a plurality of stable circumferential positions substantially free of the one or more of elastic deformation, friction, and whip impacting actuation member movement. In some embodiments, the position converter is configured to convert axial movement of the actuation member, which is subject to elastic deformation, friction, and whip, into controlled axial movement of the support member and the electrode to one of a plurality of stable axial positions.

According to some embodiments, the position converter includes a ratcheting arrangement configured to mechanically convert axial movement of the actuation member into controlled rotational movement of the support member and the electrode to one of the plurality of stable circumferential and/or axial positions. In other embodiments, the position converter includes a magnetic indexing arrangement configured to magnetically urge the support member and the electrode to one of the plurality of stable circumferential and/or axial positions. In further embodiments, the position converter includes a geometric keyed orientation mechanism configured to guide a key component of the support member into and along a keyway arrangement that limits movement of the support member and the electrode to one of the plurality of stable circumferential and/or axial positions.

In accordance with various embodiments, a catheter includes a flexible shaft having a proximal end, a distal end, a length, and a lumen extending between the proximal and distal ends. The length of the shaft is sufficient to access target tissue of the body. A slotted tube includes a proximal end, a distal end, and a length extending between the proximal and distal ends sufficient to access the target tissue. The slotted tube is dimensioned for displacement within the lumen of the shaft. The slotted tube includes a plurality of regions defined along the length of the slotted tube having disparate slot patterns associated with disparate mechanical properties including torque transmission and bending flexibility.

In some embodiments, an electrical conductor arrangement extends along the length of the slotted tube. An electrode arrangement is provided at the distal end of the slotted tube and coupled to the conductor arrangement. The electrode arrangement is configured to deliver high frequency AC energy sufficient to ablate the target tissue. In other embodiments, different types of components may be situated at the distal end of the slotted tube and provided with appropriate conductors/couplings, such as a medical device, a sensor, an electrode, an ablation device, or other medical instrument. Representative examples of components that may be situated at the distal end of the slotted tube include, for example, an ultrasound, laser, microwave, or thermal energy transfer device, some of which can be configured for one or both of ablation and monitoring/imaging.

According to some embodiments, a catheter includes a flexible shaft having a proximal end, a distal end, a length, and a lumen extending between the proximal and distal ends. The length of the shaft is sufficient to access a patient's renal artery relative to a percutaneous access location. A slotted tube includes a proximal end, a distal end, and a length extending between the proximal and distal ends sufficient to access the patient's renal artery relative to the percutaneous access location. The slotted tube is dimensioned for displacement within the lumen of the shaft and includes a plurality of regions defined along its length having disparate slot patterns associated with disparate mechanical properties including torque transmission and bending flexibility. An electrical conductor arrangement extends along the length of the slotted tube. An electrode arrangement is provided at the distal end of the slotted tube and coupled to the conductor arrangement. The electrode arrangement is configured to deliver high frequency AC energy sufficient to ablate perivascular renal nerve tissue proximate the renal artery.

Embodiments are directed to methods of ablating target tissue involving advancing an ablation electrode of an ablation catheter to a location of the body at or near target tissue to be ablated. The ablation electrode is provided at a distal end of a flexible support member. The support member is coupled to a position converter situated at a distal end of the catheter. Also coupled to the position converter is a flexible actuation member that extends from the distal end of the catheter to its proximal end. Movement of the support member and the electrode is effected by movement of the actuation member at the proximal end of the catheter, typically by a clinician or robotic system. Movement of the actuation member within the catheter's shaft is subject to one or more of elastic deformation, friction, and whip which can adversely impact control of electrode movement at or near the target tissue. Methods of the disclosure involve converting movement of the actuation member, which is adversely impacted by one or more of elastic deformation, friction, and whip, into controlled rotational movement and/or controlled axial displacement which is substantially free of any such elastic deformation, friction, and/or whip.

Methods involve controlling electrode rotation during ablation to one of a plurality of predetermined stable circumferential positions, which eliminates any adverse impact of elastic deformation, friction, and/or whip impacting movement of an actuation member at the proximal end of the catheter. Methods may also involve controlling electrode axial displacement during ablation to one of a plurality of predetermined stable axial positions, which eliminates any adverse impact of elastic deformation, friction, and or whip impacting movement of the actuation member.

These and other features can be understood in view of the following detailed discussion and the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an illustration of a right kidney and renal vasculature including a renal artery branching laterally from the abdominal aorta;

FIGS. 2A and 2B illustrate sympathetic innervation of the renal artery;

FIG. 3A illustrates various tissue layers of the wall of the renal artery;

FIGS. 3B and 3C illustrate a portion of a renal nerve;

FIG. 4 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control in accordance with various embodiments;

FIG. 5 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control using a magnetic position converter in accordance with various embodiments;

FIG. 6 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control using a magnetic position converter arranged in a helical or spiral shape in accordance with various embodiments;

FIG. 7 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control using a ratcheting position converter in accordance with various embodiments;

FIG. 8 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control using a ratcheting position converter in accordance with other embodiments;

FIG. 9 illustrates an apparatus for ablating target tissue of a vessel which incorporates precision electrode movement control using a geometric orientation position converter in accordance with other embodiments;

FIG. 10 shows the a cross-section of a geometric orientation position converter of a type shown in FIG. 9;

FIG. 11 shows a tapered entrance to a keyway structure of a geometric orientation position converter of a type shown in FIG. 9;

FIGS. 12A-12D show various sectional views of a keyway and key component having various geometries in accordance with various embodiments;

FIGS. 13A-13C and 14A-14C show various views of a keyway having various configurations in accordance with various embodiments;

FIG. 15 illustrates an ablation catheter which incorporates an elongated metallic slotted tube in accordance with various embodiments;

FIG. 16 shows various details of an elongated metallic slotted tube for use in an ablation catheter in accordance with various embodiments;

FIG. 17 shows various details of an elongated metallic slotted tube which incorporates a tension wire for controlling curvature of the slotted tube's distal tip;

FIG. 18 illustrates an ablation catheter which incorporates an elongated metallic slotted tube deployed within a patient's renal artery for ablating perivascular renal nerve tissue in accordance with various embodiments; and

FIG. 19 shows a representative high frequency AC renal therapy apparatus in accordance with various embodiments.

DISCLOSURE

Embodiments of the disclosure are directed to apparatuses and methods for ablating target tissue of the body. Embodiments of the disclosure are directed to apparatuses and methods for controlling the movement of an ablation electrode during ablation with precision. Embodiments of the disclosure are directed to apparatuses and methods for ablating perivascular renal nerves from within the renal artery using a precision electrode movement control apparatus for the treatment of hypertension.

Ablation of perivascular renal nerves can be an effective treatment for hypertension. Radiofrequency (RF) electrodes placed in the renal artery can be used to ablate the renal nerves, but with risk of injury to the artery wall. To control injury to the artery wall, one approach is to ablate at discrete locations along and around the artery. However, reliable control of electrode position has been difficult, which is adversely impacted by catheter or electrode “whip” as the electrode is moved around in the artery, for example. Also, precise control of the proximal hub of conventional ablation devices may not translate into correspondingly precise control of the tip, due to flexibility, curves, friction, and so forth. Embodiments of the disclosure provide a more precise way of controlling electrode position to desired locations in the renal artery, for example.

Various embodiments of the disclosure are directed to apparatuses and methods for renal denervation for treating hypertension. Hypertension is a chronic medical condition in which the blood pressure is elevated. Persistent hypertension is a significant risk factor associated with a variety of adverse medical conditions, including heart attacks, heart failure, arterial aneurysms, and strokes. Persistent hypertension is a leading cause of chronic renal failure. Hyperactivity of the sympathetic nervous system serving the kidneys is associated with hypertension and its progression. Deactivation of nerves in the kidneys via renal denervation can reduce blood pressure, and may be a viable treatment option for many patients with hypertension who do not respond to conventional drugs.

The kidneys are instrumental in a number of body processes, including blood filtration, regulation of fluid balance, blood pressure control, electrolyte balance, and hormone production. One primary function of the kidneys is to remove toxins, mineral salts, and water from the blood to form urine. The kidneys receive about 20-25% of cardiac output through the renal arteries that branch left and right from the abdominal aorta, entering each kidney at the concave surface of the kidneys, the renal hilum.

Blood flows into the kidneys through the renal artery and the afferent arteriole, entering the filtration portion of the kidney, the renal corpuscle. The renal corpuscle is composed of the glomerulus, a thicket of capillaries, surrounded by a fluid-filled, cup-like sac called Bowman's capsule. Solutes in the blood are filtered through the very thin capillary walls of the glomerulus due to the pressure gradient that exists between the blood in the capillaries and the fluid in the Bowman's capsule. The pressure gradient is controlled by the contraction or dilation of the arterioles. After filtration occurs, the filtered blood moves through the efferent arteriole and the peritubular capillaries, converging in the interlobular veins, and finally exiting the kidney through the renal vein.

Particles and fluid filtered from the blood move from the Bowman's capsule through a number of tubules to a collecting duct. Urine is formed in the collecting duct and then exits through the ureter and bladder. The tubules are surrounded by the peritubular capillaries (containing the filtered blood). As the filtrate moves through the tubules and toward the collecting duct, nutrients, water, and electrolytes, such as sodium and chloride, are reabsorbed into the blood.

The kidneys are innervated by the renal plexus which emanates primarily from the aorticorenal ganglion. Renal ganglia are formed by the nerves of the renal plexus as the nerves follow along the course of the renal artery and into the kidney. The renal nerves are part of the autonomic nervous system which includes sympathetic and parasympathetic components. The sympathetic nervous system is known to be the system that provides the bodies “fight or flight” response, whereas the parasympathetic nervous system provides the “rest and digest” response. Stimulation of sympathetic nerve activity triggers the sympathetic response which causes the kidneys to increase production of hormones that increase vasoconstriction and fluid retention. This process is referred to as the renin-angiotensin-aldosterone-system (RAAS) response to increased renal sympathetic nerve activity.

In response to a reduction in blood volume, the kidneys secrete renin, which stimulates the production of angiotensin. Angiotensin causes blood vessels to constrict, resulting in increased blood pressure, and also stimulates the secretion of the hormone aldosterone from the adrenal cortex. Aldosterone causes the tubules of the kidneys to increase the reabsorption of sodium and water, which increases the volume of fluid in the body and blood pressure.

Congestive heart failure (CHF) is a condition that has been linked to kidney function. CHF occurs when the heart is unable to pump blood effectively throughout the body. When blood flow drops, renal function degrades because of insufficient perfusion of the blood within the renal corpuscles. The decreased blood flow to the kidneys triggers an increase in sympathetic nervous system activity (i.e., the RAAS becomes too active) that causes the kidneys to secrete hormones that increase fluid retention and vasorestriction. Fluid retention and vasorestriction in turn increases the peripheral resistance of the circulatory system, placing an even greater load on the heart, which diminishes blood flow further. If the deterioration in cardiac and renal functioning continues, eventually the body becomes overwhelmed, and an episode of heart failure decompensation occurs, often leading to hospitalization of the patient.

FIG. 1 is an illustration of a right kidney 10 and renal vasculature including a renal artery 12 branching laterally from the abdominal aorta 20. In FIG. 1, only the right kidney 10 is shown for purposes of simplicity of explanation, but reference will be made herein to both right and left kidneys and associated renal vasculature and nervous system structures, all of which are contemplated within the context of embodiments of the disclosure. The renal artery 12 is purposefully shown to be disproportionately larger than the right kidney 10 and abdominal aorta 20 in order to facilitate discussion of various features and embodiments of the present disclosure.

The right and left kidneys are supplied with blood from the right and left renal arteries that branch from respective right and left lateral surfaces of the abdominal aorta 20. Each of the right and left renal arteries is directed across the crus of the diaphragm, so as to form nearly a right angle with the abdominal aorta 20. The right and left renal arteries extend generally from the abdominal aorta 20 to respective renal sinuses proximate the hilum 17 of the kidneys, and branch into segmental arteries and then interlobular arteries within the kidney 10. The interlobular arteries radiate outward, penetrating the renal capsule and extending through the renal columns between the renal pyramids. Typically, the kidneys receive about 20% of total cardiac output which, for normal persons, represents about 1200 mL of blood flow through the kidneys per minute.

The primary function of the kidneys is to maintain water and electrolyte balance for the body by controlling the production and concentration of urine. In producing urine, the kidneys excrete wastes such as urea and ammonium. The kidneys also control reabsorption of glucose and amino acids, and are important in the production of hormones including vitamin D, renin and erythropoietin.

An important secondary function of the kidneys is to control metabolic homeostasis of the body. Controlling hemostatic functions include regulating electrolytes, acid-base balance, and blood pressure. For example, the kidneys are responsible for regulating blood volume and pressure by adjusting volume of water lost in the urine and releasing erythropoietin and renin, for example. The kidneys also regulate plasma ion concentrations (e.g., sodium, potassium, chloride ions, and calcium ion levels) by controlling the quantities lost in the urine and the synthesis of calcitrol. Other hemostatic functions controlled by the kidneys include stabilizing blood pH by controlling loss of hydrogen and bicarbonate ions in the urine, conserving valuable nutrients by preventing their excretion, and assisting the liver with detoxification.

Also shown in FIG. 1 is the right suprarenal gland 11, commonly referred to as the right adrenal gland. The suprarenal gland 11 is a star-shaped endocrine gland that rests on top of the kidney 10. The primary function of the suprarenal glands (left and right) is to regulate the stress response of the body through the synthesis of corticosteroids and catecholamines, including cortisol and adrenaline (epinephrine), respectively. Encompassing the kidneys 10, suprarenal glands 11, renal vessels 12, and adjacent perirenal fat is the renal fascia, e.g., Gerota's fascia, (not shown), which is a fascial pouch derived from extraperitoneal connective tissue.

The autonomic nervous system of the body controls involuntary actions of the smooth muscles in blood vessels, the digestive system, heart, and glands. The autonomic nervous system is divided into the sympathetic nervous system and the parasympathetic nervous system. In general terms, the parasympathetic nervous system prepares the body for rest by lowering heart rate, lowering blood pressure, and stimulating digestion. The sympathetic nervous system effectuates the body's fight-or-flight response by increasing heart rate, increasing blood pressure, and increasing metabolism.

In the autonomic nervous system, fibers originating from the central nervous system and extending to the various ganglia are referred to as preganglionic fibers, while those extending from the ganglia to the effector organ are referred to as postganglionic fibers. Activation of the sympathetic nervous system is effected through the release of adrenaline (epinephrine) and to a lesser extent norepinephrine from the suprarenal glands 11. This release of adrenaline is triggered by the neurotransmitter acetylcholine released from preganglionic sympathetic nerves.

The kidneys and ureters (not shown) are innervated by the renal nerves 14. FIGS. 1 and 2A-2B illustrate sympathetic innervation of the renal vasculature, primarily innervation of the renal artery 12. The primary functions of sympathetic innervation of the renal vasculature include regulation of renal blood flow and pressure, stimulation of renin release, and direct stimulation of water and sodium ion reabsorption.

Most of the nerves innervating the renal vasculature are sympathetic postganglionic fibers arising from the superior mesenteric ganglion 26. The renal nerves 14 extend generally axially along the renal arteries 12, enter the kidneys 10 at the hilum 17, follow the branches of the renal arteries 12 within the kidney 10, and extend to individual nephrons. Other renal ganglia, such as the renal ganglia 24, superior mesenteric ganglion 26, the left and right aorticorenal ganglia 22, and celiac ganglia 28 also innervate the renal vasculature. The celiac ganglion 28 is joined by the greater thoracic splanchnic nerve (greater TSN). The aorticorenal ganglia 26 is joined by the lesser thoracic splanchnic nerve (lesser TSN) and innervates the greater part of the renal plexus.

Sympathetic signals to the kidney 10 are communicated via innervated renal vasculature that originates primarily at spinal segments T10-T12 and L1. Parasympathetic signals originate primarily at spinal segments S2-S4 and from the medulla oblongata of the lower brain. Sympathetic nerve traffic travels through the sympathetic trunk ganglia, where some may synapse, while others synapse at the aorticorenal ganglion 22 (via the lesser thoracic splanchnic nerve, i.e., lesser TSN) and the renal ganglion 24 (via the least thoracic splanchnic nerve, i.e., least TSN). The postsynaptic sympathetic signals then travel along nerves 14 of the renal artery 12 to the kidney 10. Presynaptic parasympathetic signals travel to sites near the kidney 10 before they synapse on or near the kidney 10.

With particular reference to FIG. 2A, the renal artery 12, as with most arteries and arterioles, is lined with smooth muscle 34 that controls the diameter of the renal artery lumen 13. Smooth muscle, in general, is an involuntary non-striated muscle found within the media layer of large and small arteries and veins, as well as various organs. The glomeruli of the kidneys, for example, contain a smooth muscle-like cell called the mesangial cell. Smooth muscle is fundamentally different from skeletal muscle and cardiac muscle in terms of structure, function, excitation-contraction coupling, and mechanism of contraction.

Smooth muscle cells can be stimulated to contract or relax by the autonomic nervous system, but can also react on stimuli from neighboring cells and in response to hormones and blood borne electrolytes and agents (e.g., vasodilators or vasoconstrictors). Specialized smooth muscle cells within the afferent arteriole of the juxtaglomerular apparatus of kidney 10, for example, produces renin which activates the angiotension II system.

The renal nerves 14 innervate the smooth muscle 34 of the renal artery wall 15 and extend lengthwise in a generally axial or longitudinal manner along the renal artery wall 15. The smooth muscle 34 surrounds the renal artery circumferentially, and extends lengthwise in a direction generally transverse to the longitudinal orientation of the renal nerves 14, as is depicted in FIG. 2B.

The smooth muscle 34 of the renal artery 12 is under involuntary control of the autonomic nervous system. An increase in sympathetic activity, for example, tends to contract the smooth muscle 34, which reduces the diameter of the renal artery lumen 13 and decreases blood perfusion. A decrease in sympathetic activity tends to cause the smooth muscle 34 to relax, resulting in vessel dilation and an increase in the renal artery lumen diameter and blood perfusion. Conversely, increased parasympathetic activity tends to relax the smooth muscle 34, while decreased parasympathetic activity tends to cause smooth muscle contraction.

FIG. 3A shows a segment of a longitudinal cross-section through a renal artery, and illustrates various tissue layers of the wall 15 of the renal artery 12. The innermost layer of the renal artery 12 is the endothelium 30, which is the innermost layer of the intima 32 and is supported by an internal elastic membrane. The endothelium 30 is a single layer of cells that contacts the blood flowing though the vessel lumen 13. Endothelium cells are typically polygonal, oval, or fusiform, and have very distinct round or oval nuclei. Cells of the endothelium 30 are involved in several vascular functions, including control of blood pressure by way of vasoconstriction and vasodilation, blood clotting, and acting as a barrier layer between contents within the lumen 13 and surrounding tissue, such as the membrane of the intima 32 separating the intima 32 from the media 34, and the adventitia 36. The membrane or maceration of the intima 32 is a fine, transparent, colorless structure which is highly elastic, and commonly has a longitudinal corrugated pattern.

Adjacent the intima 32 is the media 33, which is the middle layer of the renal artery 12. The media is made up of smooth muscle 34 and elastic tissue. The media 33 can be readily identified by its color and by the transverse arrangement of its fibers. More particularly, the media 33 consists principally of bundles of smooth muscle fibers 34 arranged in a thin plate-like manner or lamellae and disposed circularly around the arterial wall 15. The outermost layer of the renal artery wall 15 is the adventitia 36, which is made up of connective tissue. The adventitia 36 includes fibroblast cells 38 that play an important role in wound healing.

A perivascular region 37 is shown adjacent and peripheral to the adventitia 36 of the renal artery wall 15. A renal nerve 14 is shown proximate the adventitia 36 and passing through a portion of the perivascular region 37. The renal nerve 14 is shown extending substantially longitudinally along the outer wall 15 of the renal artery 12. The main trunk of the renal nerves 14 generally lies in or on the adventitia 36 of the renal artery 12, often passing through the perivascular region 37, with certain branches coursing into the media 33 to enervate the renal artery smooth muscle 34.

Embodiments of the disclosure may be implemented to provide varying degrees of denervation therapy to innervated renal vasculature. For example, embodiments of the disclosure may provide for control of the extent and relative permanency of renal nerve impulse transmission interruption achieved by denervation therapy delivered using a treatment apparatus of the disclosure. The extent and relative permanency of renal nerve injury may be tailored to achieve a desired reduction in sympathetic nerve activity (including a partial or complete block) and to achieve a desired degree of permanency (including temporary or irreversible injury).

Returning to FIGS. 3B and 3C, the portion of the renal nerve 14 shown in FIGS. 3B and 3C includes bundles 14 a of nerve fibers 14 b each comprising axons or dendrites that originate or terminate on cell bodies or neurons located in ganglia or on the spinal cord, or in the brain. Supporting tissue structures 14 c of the nerve 14 include the endoneurium (surrounding nerve axon fibers), perineurium (surrounds fiber groups to form a fascicle), and epineurium (binds fascicles into nerves), which serve to separate and support nerve fibers 14 b and bundles 14 a. In particular, the endoneurium, also referred to as the endoneurium tube or tubule, is a layer of delicate connective tissue that encloses the myelin sheath of a nerve fiber 14 b within a fasciculus.

Major components of a neuron include the soma, which is the central part of the neuron that includes the nucleus, cellular extensions called dendrites, and axons, which are cable-like projections that carry nerve signals. The axon terminal contains synapses, which are specialized structures where neurotransmitter chemicals are released in order to communicate with target tissues. The axons of many neurons of the peripheral nervous system are sheathed in myelin, which is formed by a type of glial cell known as Schwann cells. The myelinating Schwann cells are wrapped around the axon, leaving the axolemma relatively uncovered at regularly spaced nodes, called nodes of Ranvier. Myelination of axons enables an especially rapid mode of electrical impulse propagation called saltation.

In some embodiments, a treatment apparatus of the disclosure may be implemented to deliver denervation therapy that causes transient and reversible injury to renal nerve fibers 14 b. In other embodiments, a treatment apparatus of the disclosure may be implemented to deliver denervation therapy that causes more severe injury to renal nerve fibers 14 b, which may be reversible if the therapy is terminated in a timely manner. In preferred embodiments, a treatment apparatus of the disclosure may be implemented to deliver denervation therapy that causes severe and irreversible injury to renal nerve fibers 14 b, resulting in permanent cessation of renal sympathetic nerve activity. For example, a treatment apparatus may be implemented to deliver a denervation therapy that disrupts nerve fiber morphology to a degree sufficient to physically separate the endoneurium tube of the nerve fiber 14 b, which can prevent regeneration and re-innervation processes.

By way of example, and in accordance with Seddon's classification as is known in the art, a treatment apparatus of the disclosure may be implemented to deliver a denervation therapy that interrupts conduction of nerve impulses along the renal nerve fibers 14 b by imparting damage to the renal nerve fibers 14 b consistent with neruapraxia. Neurapraxia describes nerve damage in which there is no disruption of the nerve fiber 14 b or its sheath. In this case, there is an interruption in conduction of the nerve impulse down the nerve fiber, with recovery taking place within hours to months without true regeneration, as Wallerian degeneration does not occur. Wallerian degeneration refers to a process in which the part of the axon separated from the neuron's cell nucleus degenerates. This process is also known as anterograde degeneration. Neurapraxia is the mildest form of nerve injury that may be imparted to renal nerve fibers 14 b by use of a treatment apparatus according to embodiments of the disclosure.

A treatment apparatus may be implemented to interrupt conduction of nerve impulses along the renal nerve fibers 14 b by imparting damage to the renal nerve fibers consistent with axonotmesis. Axonotmesis involves loss of the relative continuity of the axon of a nerve fiber and its covering of myelin, but preservation of the connective tissue framework of the nerve fiber. In this case, the encapsulating support tissue 14 c of the nerve fiber 14 b are preserved. Because axonal continuity is lost, Wallerian degeneration occurs. Recovery from axonotmesis occurs only through regeneration of the axons, a process requiring time on the order of several weeks or months. Electrically, the nerve fiber 14 b shows rapid and complete degeneration. Regeneration and re-innervation may occur as long as the endoneural tubes are intact.

A treatment apparatus may be implemented to interrupt conduction of nerve impulses along the renal nerve fibers 14 b by imparting damage to the renal nerve fibers 14 b consistent with neurotmesis. Neurotmesis, according to Seddon's classification, is the most serious nerve injury in the scheme. In this type of injury, both the nerve fiber 14 b and the nerve sheath are disrupted. While partial recovery may occur, complete recovery is not possible. Neurotmesis involves loss of continuity of the axon and the encapsulating connective tissue 14 c, resulting in a complete loss of autonomic function, in the case of renal nerve fibers 14 b. If the nerve fiber 14 b has been completely divided, axonal regeneration causes a neuroma to form in the proximal stump.

A more stratified classification of neurotmesis nerve damage may be found by reference to the Sunderland System as is known in the art. The Sunderland System defines five degrees of nerve damage, the first two of which correspond closely with neurapraxia and axonotmesis of Seddon's classification. The latter three Sunderland System classifications describe different levels of neurotmesis nerve damage.

The first and second degrees of nerve injury in the Sunderland system are analogous to Seddon's neurapraxia and axonotmesis, respectively. Third degree nerve injury, according to the Sunderland System, involves disruption of the endoneurium, with the epineurium and perineurium remaining intact. Recovery may range from poor to complete depending on the degree of intrafascicular fibrosis. A fourth degree nerve injury involves interruption of all neural and supporting elements, with the epineurium remaining intact. The nerve is usually enlarged. Fifth degree nerve injury involves complete transection of the nerve fiber 14 b with loss of continuity.

Referring now to FIG. 4, a distal end of an ablation catheter 100 is shown deployed in a renal artery 12 of a patient. According to this embodiment, the ablation catheter 100 includes a flexible shaft 202 and a lumen 203 that extends along the length of the shaft 202. The length of the shaft 202 is preferably sufficient to access a desired location of the body, such as the patient's renal artery 12 as shown in this illustrative example. A flexible actuation member 206 is provided within the lumen 203 of the shaft 202 and extends to the proximal end of the shaft 202. The actuation member 206 is movable within the lumen 203 of the shaft 202 and subject to one or more of elastic deformation, friction, and with along its length during movement within the shaft's lumen 203. The proximal end of the actuation member 206 may be fitted with a handle or other arrangement that facilitates rotational and axial movement of the actuation number 206 by a clinician or a robotic system.

The embodiment shown in FIG. 4 further includes a flexible support member 205 coupled to a distal end of the actuation member 206 and is configured to be extendable beyond the distal tip 207 of the shaft 202 and into a lumen 13 of the renal artery 12. An electrode 208 is provided at a distal end of the support member 205 and configured to contact a wall 15 of the renal artery 12 and deliver high-frequency AC energy sufficient to ablate perivascular renal nerve tissue 37 proximate the electrode 208. The support member 205 preferably has a curved shape configured to urge the electrode 208 into contact with the wall 15 of the renal artery 12. A position converter 204 is provided at the distal end of the shaft 202 and coupled to the distal end of the actuation member 206 and a proximal end of the support member 205.

The position converter 204 is configured to convert movement of the actuation member 206 into at least controlled rotational movement of the support member 205 and the electrode 208 to one of a plurality of stable circumferential positions substantially free of one or more of elastic deformation, friction, and whip impacting actuation member movement. The position converter 204 may also be configured to convert movement of the actuation member 206 into controlled axial movement of the support member 205 and the electrode 208 to one of a plurality of stable axial position. In some embodiments, the actuation member 206 and the support member 205 define a continuous member, and the position converter 204 acts upon this continuous member. In other embodiments, the actuation member 206 and the support member 205 define separate members, each having a proximal end and a distal end. In such embodiments, the proximal end of the support member 205 and the distal end of the actuation member 206 are coupled via the position converter 204.

Turning now to FIG. 5, there is illustrated a position converter 204 which includes a magnetic indexing arrangement 201 provided at a distal end of an ablation catheter 100 in accordance with various embodiments. The position converter 204 shown in FIG. 5 provides for magnetic alignment of the support member 205 and the electrode 208 using a discrete magnetically actuated indexing mechanism, so that the electrode 208 can be positioned at the appropriate locations along and around the wall 15 of the renal artery 12. The distal end of the support member 205 is typically curved, so that the electrode 208 makes good contact with the vessel wall 15. The magnetic indexing arrangement 201 is configured to magnetically urge the support member 205 and the electrode 208 to one of a plurality of stable circumferential positions. In some embodiments, a representative example of which is shown in FIG. 5, the magnetic indexing arrangement 204 is configured to magnetically urge the support member 205 and the electrode 208 to one of a plurality of stable circumferential and axial positions.

A magnet 216 is situated on the actuation member 206 at a desired location. Magnets 215 situated on the catheter's shaft 202 interact with the actuation member magnet 216 to urge the support member 205 and electrode 208 into only specific stable locations. The support member 205 and electrode 208 are advanced and rotated between the stable locations by the clinician or a robotic system. Advantageously, only rough imaging information is required to verify that the electrode 208 is in the desired location, since the magnetic forces prevent small misalignments, and the electrode 208 is stable only in a substantially different position which could easily be seen on an imaging device.

According to a representative method of use, the support number 205 and electrode 208 are advanced to the distal-most extent, at which point the electrode 208 is activated with the magnets 216, 215 aiding in circumferential alignment at a first treatment location. The support member 205 may be withdrawn a short distance into the catheter's shaft 202 and the electrode 208 activated again, with the magnets 216, 215 aiding in positioning the electrode 208 at a circumferential orientation different from the first location, and so forth until ablation has been performed at all desired treatment locations.

According to various embodiments, the shaft 202 of the ablation catheter 100 includes multiple sets of magnets 215 at different axial locations, with polarities arranged at different circumferential points at the different axial locations. In the embodiment illustrated in FIG. 5, for example, there are four axial positions indicated (axial positions #1, #2, #3, and #4) which are located 90° apart from one another. The polarity of each magnet of the shaft magnet arrangement 215 and that of the support member magnet arrangement 216 is indicated as N (North) or S (South).

Pairs of magnets 215 are situated circumferentially offset from one another by 90° at the four axial positions #1, #2, #3, and #4, each of which defines a magnetically stable position. A single magnet is shown situated on the support member 205. The support member 205 and electrode 208 are urged by the magnetic forces to orient at these axial positions to four different circumferential directions. For additional alignment force, the support member 205 can include multiple magnets 216 oriented appropriately so that the multiple sets of shaft magnets 215 and multiple support member magnets 216 interact.

When the support member 205 is advanced to one axial position, the magnets 215 on the shaft 202 interact with the magnet 216 on the support member 205 to urge the electrode 208 to one circumferential location. When the support number 205 is advanced or retracted to a different axial position, the magnets 215 on the shaft 202 interact with the magnet 216 on the support member 205 to urge the electrode 208 to a different circumferential location. In this way, a desired number (e.g., 2 to 10) discrete ablation sites, for example, can be obtained at predetermined axial and circumferential locations. Any one spot in the renal artery 12 would have minor or small areas of injury, and any subsequent healing response or stenosis would be insignificant.

It is understood that the number of magnet pairs and location of these pairs (circumferentially and/or axially) on the shaft 202 can differ from that shown in FIG. 5 to achieve a desired number of magnetically stable positions at desired circumferential and/or axial directions. For example, six magnetically stable positions can be achieved by situating a pair of magnets 205 on the shaft at desired spaced-apart axial positions circumferentially offset from one another by 60°. By way of further example, eight magnetically stable positions can be achieved by situating a pair of magnets 205 on the shaft at desired spaced-apart axial positions circumferentially offset from one another by 45°. In some embodiments, it may be desirable to provide controlled circumferential positioning of the support member 205 at a single axial location, such as for creating a circumferential lesion in target tissue. In such embodiments, pairs of magnets would be situated circumferentially offset from one another by 90° or other desired angle at a specified axial location of the shaft 202.

In accordance with other embodiments, and with reference to FIG. 6, a catheter, such as a guiding catheter, includes a magnetic indexing arrangement having a helical configuration, so that the support member 205 and electrode 208 are guided along a predictable helical path. The distal end of the shaft 202 is preferably fashioned to include a pre-form a helical shape. Additional magnetic or other alignment or indexing features can be incorporated to provide limited axial stability as well, so that a number of discrete ablation locations can be obtained, and spaced apart as desired.

The magnets 215 in the catheter's shaft 202 can be continuous, or a series of oriented magnets. The magnets on the support member 205 can similarly be continuous or a series of oriented magnets. According to some embodiments, when the support member 205 is advanced or retracted by corresponding movement of the actuation member 206, the support member 205 rotates in a predictable helical path, providing position control for the electrode 208 along a predictable helical path on the artery wall 15. In other embodiments, when the support member 205 is rotated by corresponding movement of the actuation member 206, the support member 205 rotates in a predictable circumferential path, providing position control for the electrode 208 along a predictable circumferential path on the artery wall 15. Intermittent application of RF energy to electrical conductors coupled to the electrode 208 produces a helical pattern or a circumferential pattern of separate ablation zones. In some embodiments, a physical helical groove can be provided to further aid in orienting the support member 205 and electrode 208 along a predictable helical path.

If alignment mechanisms were incorporated near the proximal hub of the ablation catheter as in the case of conventional approaches, curvature, poor torque transmission and/or friction could significantly reduce the effectiveness of such alignment mechanisms. Because the present embodiments use magnetic alignment forces that are applied near the distal end of the shaft 202 and actuation member 206, any elastic deformation in the bulk of the shaft 202 or actuation member 206 would have no significant effect on electrode 208 positioning (rotational and/or axial positioning).

Multiple magnets 215 around the circumference of the catheter's shaft 205 can be used to create multiple discrete stable locations of the support member 205 and electrode 208 at the same axial location, so that two or more small ablation spots can be obtained at that axial location, spaced circumferentially apart to control artery wall injury. An additional set of magnets 216 can be used to similarly guide the support member 205 and electrode 208 to two or more stable circumferential locations at a different axial location. In this way, less axial distance is required to obtain discrete areas of ablation, which may be an advantage in anatomies with short renal artery trunks. Mechanical guides near the end of a catheter's shaft 202 can be used to control the location or orientation of the electrode 208. Mechanical guides and magnetic guides can be used in combination.

In accordance with various embodiments, apparatuses and methods provide for circumferential position control of an RF electrode placed in vessel of the body using a ratcheting arrangement provided at a distal end of the shaft of an ablation catheter. An ablation catheter employing a ratcheting arrangement that provides for precision control of an electrode's circumferential position is particularly useful for ablating perivascular renal nerves adjacent the renal artery of the patient. To avoid renal artery stenosis, discrete zones of ablation can be created by moving an RF electrode axially and/or circumferentially in the renal artery.

According to various embodiments, a ratcheting position control arrangement includes a spring-loaded rotating ratcheting element, like portions of a ballpoint pen retraction mechanism. In a pen, for example, the ink reservoir typically does not rotate, but components of the ratcheting mechanism do. In some embodiments, the ratcheting position control arrangement can be actuated to move the ablation electrode to a number of discrete circumferential stable locations were ablation is performed. In such embodiments, each actuation of the ratcheting causes the ablation electrode to move from one stable circumferential location to the next stable circumferential location. This process is repeated until ablation has been performed at each of the stable circumferential locations.

In accordance with other embodiments, combined axial and circumferential positioning of the ablation electrode is achieved. In embodiments where the rotation feature of the ratchet mechanism is combined with the axial displacement feature (like the pen retracting), the ablation electrode is moved both axially and circumferentially between discrete stable positions. With each actuation of the ratchet mechanism, the electrode moves to a new stable position. At each stable position, RF energy is delivered by the ablation electrode to create a controlled region of injury. The combined effect of separate injury regions causes ablation of the perivascular renal nerves with beneficial effect on hypertension, with limited areas of renal artery injury. With this approach, a predetermined number of discrete ablation sites can be obtained at predetermined axial and circumferential locations. Any one spot in the renal artery would have minor or small areas of injury, and any subsequent healing response or stenosis would be insignificant.

Cooling can be incorporated into the ablation catheter design to further reduce renal artery injury. For example, the ablation catheter can be implemented as an infusion catheter, in which a biocompatible cooling fluid is transported from a proximal end of the catheter to the distal end of the catheter. Provision of cooling at the electrode-tissue interface can reduce the risk of thermal injury to the renal artery wall. Various other cooling approaches are contemplated.

In apparatuses of the present disclosure, the support member to which the ablation electrode is mounted can be coupled to the rotating ratcheting element so that it rotates 60 or 90 degrees (or other predetermined angles), for example, at each actuation of the ratchet mechanism. When the actuation member is pushed or pulled at its proximal and to overcome a spring force, a rotating ratchet mechanism is actuated which rotates the support member and electrode to the next stable circumferential position.

In other embodiments, combined axial and circumferential positioning is provided. In configurations where the rotation feature of the ratchet mechanism is combined with the axial displacement feature (like the pen retracting), the support member and electrode move both axially and circumferentially between discrete positions. Rather than pushing or pulling on the RF electrode wire to activate the ratchet mechanism, a separate control wire or tube can be provided.

Referring now to FIGS. 7 and 8, there is shown a position converter implemented as a ratcheting arrangement 204 in accordance with various embodiments. The ratcheting arrangement 204 is provided at a distal end of the shaft 202 and has a proximal end and a distal end. A spring arrangement 212 is situated at the proximal end of the ratcheting arrangement 204. At the distal end of the ratcheting arrangement 204, a keyway arrangement 200 preferably includes a multiplicity of keyways 210. A keyway 210 defines a guide path that constrains the movement of the support member 205 and electrode 208 to a predetermined path, such as by limiting the rotational and/or axial travel of the support member 205 and electrode 208.

Typically, the ratcheting arrangement 204 incorporates a multiplicity of keyways 210, although a single keyway 210 may be appropriate in some applications. The keyways 210 are configured to receive a key component 207 provided on the distal end of the actuation member 206. Each of the keyways 210 has opposing end locations, each of which can define a predetermined stable circumferential and/or axial position for orienting the support member 205 and the electrode 208. A multiplicity of circumferentially spaced keyways 210 having an axial aspect may be incorporated in the ratcheting arrangement 204. Depending on the configuration of the ratcheting arrangement 204, a desired number of discrete ablation sites can be obtained, such as between two and eight discrete ablation sites, at predetermined axial and circumferential locations. Various additional components including gear or spring elements can be incorporated into the ratcheting arrangement 204 in accordance with various embodiments.

FIG. 7 further shows a control member 209 which can be used to actuate the ratcheting arrangement 204. The control member 209 can be implemented as a control wire or, as shown in FIG. 7, a control tube. In embodiments where the ratcheting arrangement 204 provides for rotational positioning of the support member 205 and electrode 208 with no axial positioning provided, the control member 209 need not be included, and an actuation member 206 of a type previously described herein can be used to actuate the ratcheting arrangement 204. In such embodiments, actuation of the ratcheting mechanism 204 can be accomplished by pushing and pulling the actuation member 206. In embodiments where the ratcheting arrangement 204 provides for both rotational and axial positioning of the support member 205 and electrode 208, the separate control member 209 may be employed in the actuation of the ratcheting arrangement 204.

FIG. 8 schematically illustrates the controlled movement of the ablation electrode 208 between four stable positions located circumferentially and axially apart from one another. The electrode 208 follows a generally zigzag path from one stable position to another resulting from actuation of the ratcheting mechanism 204 and constrained movement dictated by the keyways 210. When the electrode 208 reaches each of the stable positions, the support member 205 has a spring bias that forces the electrode 208 against the wall 15 of the renal artery 12. Depending on the keyway design, the electrode 208 may or may not maintain continuous contact with the renal artery wall 15 when traversing a path between stable positions.

The ablation procedure preferably begins by advancing the support member 205 and electrode 208 to its distal-most position, which is shown as stable position #1 in FIG. 8. In general, the support member 205 and electrode 208 are moved from one stable position to the next stable position in response to each actuation of the ratcheting arrangement 204, which in this illustrative embodiment is accomplished using the control member 209. With the electrode 208 located at stable position #1, RF energy is delivered to the electrode 208. After completing ablation at stable position #1, the control member 209 is pushed, causing the support member 205 and electrode 208 to traverse along path-A. The control member 209 is pushed until a spring force produced by the spring arrangement 212 is overcome, at which point the electrode 208 is located at stable position #2. RF energy is delivered to the electrode 208 at stable position #2 until ablation at this location is completed. Pushing the control member 209 causes the electrode 208 to move from stable position #2 to stable position #3 along path-B. RF energy is delivered to the electrode 208 at stable position #3 until ablation at this location is completed. The control member 209 is again pushed by the clinician or robotic system causing the electrode 208 to move from stable position #3 to stable position #4 along path-C. RF energy is delivered to the electrode 208 at stable position #4 until ablation at this location is completed. The electrode 208 can be moved to its initial starting location at stable position #1 by again pushing the control member 209, causing the electrode 208 to move from stable position #3 to stable position #4 along path-D. After completing ablation at all stable locations, the support member 205 electrode 208 can be retracted into the lumen of the shaft 202.

According to various embodiments, and with reference to FIGS. 9-11, a position converter of an ablation catheter 100 includes a geometric keyed orientation mechanism 220 provided at the distal end of a guiding catheter or sheath, and further includes corresponding key components 207 provided on the actuation member 206. The geometric keyed orientation mechanism 220 is configured to guide a key component 207 of the actuation member 206 into and along a keyway arrangement 221 that limits movement of the support member 205 and the electrode 208 to one of a plurality of stable circumferential positions. In some embodiments, the geometric keyed orientation mechanism 220 is configured to guide a key component 207 of the actuation member 206 and the electrode 208 to one of a plurality of stable circumferential positions and one of a plurality of stable axial position.

The keyway arrangement 221 includes a multiplicity of axial space-apart keyways 210 each comprising a tapered entrance 222 configured to guide the key component 208 into alignment with each of the keyways 210. The tapered entrance 222 of each keyway 210 can be configured to guide the key component 208 into the keyway 210 if the relative orientation is within +/−45, 60 or 90 degrees (or some other angle range), for example. FIG. 11 illustrates that only a rough orientation of the actuation member 206 needs to be transmitted from the proximal end of the actuation member 206 to the geometric keyed orientation mechanism 220, since the tapered entrance 222 provides for fine orientation adjustments of the support member 205 and electrode 208. For example, FIG. 11 shows misalignment between a key component 207 of the actuation member 206 and a keyway 210 which provides a desired electrode orientation. Gross misalignment between the key component 207 and the keyway 210 is corrected by the tapered entrance 222, which channels the misaligned key component 207 into proper alignment with the keyway 210.

In some embodiments, the keyway arrangement 221 includes a multiplicity of space-apart keyways 210, with alternate keyways 210 of the keyway arrangement 221 having differing lengths. In other embodiments, the keyway arrangement 221 includes a multiplicity of circumferentially and axially spaced-apart keyways 210. The keyways arrangement 221 may be formed with keyways 210 having varying geometries. For example, as with reference to FIGS. 12A-12D, keyways 210 may have one of an elliptical, square, rectangular, triangular, or other geometric cross-section that provides stability to properly orient the support member 205 and electrode 208.

In some embodiments, and with reference to FIGS. 13A-14C, a helical keyway or a zigzag keyway can be used, with the clinician providing slight bias or rough orientation to move the actuation member 206 to the next desired location, and the refined orientation is provided by the keyway/keyway component geometry. A keyway transition feature, such as a short axial slot 212, can be incorporated into a keyway arrangement 221 to provide tactile feedback indicating a transition from one keyway 210 to the next keyway 210.

In some configurations, pushing or pulling on the actuation member 206 relative to the guiding catheter or sheath 202 moves the keyed components between the stable locations. FIGS. 13A-14C schematically illustrates various configurations of keyways 210. In FIGS. 13A-14C, the generally cylindrical keyway configurations have been opened up for ease of illustration. In addition to the configurations illustrated in FIGS. 13A-14C, helical patterns, or combinations of various patterns can be used to control electrode positions to a set of limited-stability locations.

Maintaining good contact with the artery wall during ablation of perivascular renal nerves for hypertension control has been difficult. If contact is variable, the tissue temperatures are not well controlled, and an ablative temperature may not be achieved in the target tissue, while temperature in other areas, such as portions of the artery wall, may deviate enough to cause unwanted arterial tissue injury. For ideal anatomy, good vessel apposition can be achieved more easily. However, especially with tortuous or diseased renal arteries, there can be very poor contact to effectively and predictably transfer heat, electrical current, or other energy from an ablation device to the tissue. Conventional RF electrode wires have not provided the required balance of pushability, torque control, and flexibility along the length to provide for reliable contact of the electrode with the vessel wall.

Apparatuses and methods of the disclosure provide for improved directability of intra-arterial RF electrode wires for better apposition to the artery wall during renal nerve ablation. According to various embodiments, and with reference to FIG. 15, and ablation catheter 100 includes a flexible shaft 202 having a lumen dimensioned to receive an RF electrode wire in the form of a slotted tube structure 230. In embodiments involving renal denervation, the shaft 202 has a proximal end, a distal end, a length, and a lumen extending between the proximal and distal ends. The length of the shaft 202 is sufficient to access a patient's renal artery relative to a percutaneous access location. The slotted tube 230 has a proximal end, a distal end, and a length extending between the proximal and distal ends sufficient to access the patient's renal artery relative to the percutaneous access location. The slotted tube 230 is dimensioned for displacement within the lumen of the shaft 202.

The slotted tube 230, according to various embodiments, comprises a multiplicity of regions defined along its length. Each of the slotted tube regions has disparate slot patterns associated with disparate mechanical properties, such as torque transmission and bending flexibility. An electrical conductor arrangement 232 extends along the length of the slotted tube 230. An electrode arrangement 208 is provided at a distal end of the slotted tube 230 and is coupled to the conductor arrangement 232. Electrode arrangement 208 is configured to deliver high-frequency AC energy sufficient to ablate perivascular renal nerve tissue proximate the renal artery.

According to various ablation methods, a guiding catheter or sheath 100 is directed to a renal artery and placed at a desired location and orientation within the artery. The slotted tube 230 is advanced within the lumen of the shaft 202 of the guiding catheter and positioned in contact with the renal artery wall at the treatment location. The RF electrode 208 is energized to cause ablation of perivascular renal nerves. After completing ablation at this site, the guiding catheter or sheath 100 is moved to another location within the renal artery, and the RF electrode 208 is energized to cause ablation of perivascular renal nerves adjacent this site. This process is repeated for the current renal artery and then the contra-lateral renal artery until all desired renal artery sites have been subject to ablation. The ablation catheter arrangement is that removed from the patient's body.

FIG. 16 shows various features of a slotted tube 230 in accordance with various embodiments. According to some embodiments, the slotted tube 230 is formed to include a metallic slotted tube shaft. In other embodiments, the slotted tube 230 is formed from material other than metal. For example, the slotted tube 230 may be constructed as a slotted polymer tube. In other configurations, the slotted tube 230 may incorporate ringed, helical, or braided components. In some configurations, fiber-reinforced components may be used to construct the slotted tube 230. Also, separate components for each segment of the slotted tube 230 may be bonded together, for example. The slotted tube configuration provides superior torque control for accurate positioning and orientation of the electrode, while maintaining sufficient flexibility to facilitate access to the target site.

As is shown in FIG. 16, an RF electrode 208 is attached at the distal tip of the slotted tube 230. Insulated electrical conductor wires 232 pass through the central lumen of the slotted to 230 and provide power to the RF electrode 208. The proximal ends of the electrical conductor wires 232 connect to an external power supply and control unit.

In some embodiments, the slotted to 230 is lined with a thin polymeric tube 234 that surrounds the slotted tube 230 other than at one or more perfusion locations at the distal end of the slotted tube 230. For example, short portions of the slotted tube 230 near the distal end may be purposefully devoid of the polymeric tube 234. Alternatively, the polymeric tube 230 can extend as far as the electrode 208, and include perforations or apertures to define a perfusion region. The polymeric tube 234 forms a fluid-type lumen around the slotted tube 230 through which a liquid can be transported between the proximal and distal ends of the slotted to 230. For example, a cooling fluid may be transported from a fluid source at the proximal end of the slotted to 230 and transported to the distal perfusion region of the slotted tube 230 proximate the electrode 208. A biocompatible cooling fluid may be used to provide cooling at the electrode-tissue interface. The fluid-tight lumen surrounding the slotted tube 230 may also be used for flushing without leakage through the slots in the tube 230.

In some configurations, the slotted tube 230 is used to conduct electric current to a unipolar electrode 208, with the return path to a remote pad in contact with the patient's skin. In other configurations, the slotted tube 230 includes multiple electrodes 208 situated near the distal end, with insulated electrical conductor wires used to power the multiple electrodes. In still other configurations, one or more bipolar RF electrode pairs may be situated at the distal end of the slotted tube 230, with insulated electrical conductor wires as required.

One or more sensors near the distal end, such as temperature sensors, can be included, with insulated electrical conductor wires used for power or signal transfer for the sensors. For example, a temperature sensor may be situated at or near the electrode 208. The temperature sensor provides sensing of a temperature at the electrode-tissue interface during ablation. Signals generated by the temperature sensor can be transmitted to the distal end of the catheter 100 using conductor wires that extend through the slotted tube 230. Temperature signals can be used by an external power and control system to automatically or semi-automatically control power delivery (and cooling fluid if desired) to the electrode 208 during an ablation procedure.

FIG. 17 illustrates a slotted tube 230 with an active curve mechanism in accordance with various embodiments. The illustrative example shown in FIG. 17 includes a tension wire 238 coupled to the distal tip of the slotted tube 230 and extending between the distal tip and the proximal end of the slotted tube 230. The tension wire 238 causes the distal tip of the slotted tube 232 to curve in response to a tensioning force applied to the proximal end of the tension wire 238.

The slot pattern of the slotted tube 230 can be configured to obtain desired mechanical properties. For example, the slot pattern can vary, to provide tuned properties in different regions, and with transition zones to avoid abrupt property changes which could result in kinking or other problems. In general, the entire length of the slotted tube 230 is typically configured for good torque transmission so that the clinician can control the circumferential orientation of the electrode 208, with a moderate amount of bending flexibility to allow advancement through sheaths and the vasculature. In a tip region of the slotted tube 230, a short region of increased bending stiffness can be incorporated so that a tip curve is maintained to aid in directing the electrode 208 to contact the artery wall. The tip curve can be maintained by spring-like elasticity in this region. In an intermediate region of the slotted tube 230 near the tip region, enhanced bending stiffness can be incorporated so that the slotted tube 230 can easily bend at the renal artery ostium to minimize arterial trauma, even though the tip curve is maintained, and the enhanced torque transmission is used to control electrode orientation within the renal artery.

To further control mechanical properties at the tip region, the slot pattern of the slotted tube 230 can be tuned to provide a biased flexibility, such as to allow the tip curve to bend the electrode 208 outwardly towards the vessel wall in one plane, but to resist bending in an orthogonal plane, so that the circumferential positioning of the electrode 208 is well controlled. In some embodiments, a curve portion near the distal end of the slotted tube 230 can have a different slotted tube structure, or no slots, and provides an orientation curve so that the electrode 208 can be pressed towards the artery wall. The curved tip can have a preset curved shape which is maintained by forming or treating this region to a permanent curve, or a shape-memory material can be used to achieve the curve using thermal or other control. Alternatively, an active-curve mechanism can be provided, such as by using a biased tube structure and a tension wire 238 to actively flex the curve portion when desired. Other mechanisms can be used to control the curved tip portion, such as torsional bias, external sheath constraint, and a push-wire, for example.

A distinctive aspect of a slotted tube 230 in accordance with various embodiments is that its construction effectively decouples flexural and torsional stiffness of this structure. This provides for the “tuning” (e.g., optimizing or customization) of various mechanical properties of the slotted tube 230 at different axial locations along its length. Moreover, flexural stiffness can be non-linear due to interference between adjacent ribs of the slotted tube 230. The slotted tube 230 can be customized to incorporate different slot patterns at different axial locations along its length to achieve desired mechanical properties that may have at least some of the following attributes:

-   -   Single Plane Symmetry (slotted tube flexing in a preferred         direction): This attribute imparts a directional steering         capability, which can be achieved by providing longitudinally         continuous spines within the slotted tube structure. If the         spines are off-set from the axis, the shaft of the slotted tube         230 will have a preferred direction within the symmetry plane.     -   Multiple Symmetry Plane: If more than 2 axial spines are         present, there will be multiple symmetry planes. The effect will         be most pronounced with the presence of an even number of         spines. This is a form of geometric keying.     -   Axisymmetric Flexibility: Adjacent connectors can be staggered         so that axially uniform flexibility is provided with minimal         loss of torsional rigidity. This may be viewed as a “flex         coupler” design. If connecting spines precess or spiral along         the axis, the shaft of the slotted tube 230 will tend to deform         in a similar manner.

The preferred distribution of properties along the slotted tube 230 is typically dependent on the desired electrode configuration. Consider an electrode of a slotted tube 230 arranged tangent to the surface with an S-curve. The portion of the slotted tube 230 with the S-curve may have the following attributes:

-   -   a primary curve (closest to tip) having highly flexible         axisymmetric flexure.     -   a pull wire terminates between the primary and a secondary         curve.     -   the secondary curve having single plane symmetry to provide         directional steering and stability.     -   a tertiary curve which is axisymmetric with moderate flexure to         provide torque transmission and smooth axial control.

It is noted that for acute tip contact angles, the primary curve can be eliminated. Also, multi-plane symmetry in the tertiary curve provides a rotary detent effect. The effect is exaggerated if bending is concentrated in a short section of the slotted tube 230.

In accordance with an associated method, the slotted tube 230 can be guided to a treatment location in a renal artery using a guiding catheter or sheath, utilizing the enhanced torque control of the slotted tube 230 to orient the electrode 208 to a desired position in good contact with the artery wall. With the electrode 208 positioned against the artery wall at a desired site, RF energy is used to ablate perivascular renal nerves. An external control unit is used to energize the electrode 208, which can be configured for operation in either a unipolar mode (using an external pad return electrode) or a bipolar mode.

In accordance with various embodiments, and with reference to FIG. 18, the slotted tube 230 is dimensioned for displacement within the lumen of the shaft of a guiding catheter or sheath, and includes a plurality of regions defined along its length having disparate slot patterns associated with disparate mechanical properties including torque transmission and bending flexibility. The multiplicity of regions defined along the length of the slotted tube 230 include a proximal region (4), a turn region (3), and a tip region (1). The proximal region (4) is defined between the proximal end of the slotted tube 230 and the turn region (3). The proximal region (4) preferably has a slot pattern configured to provide enhanced torque transmission relative to bending flexibility.

The turn region (3) preferably has a slot pattern configured to provide enhanced bending flexibility relative to torque transmission to facilitate bending of the slotted tube 230 around an aortorenal junction 21 at the ostium of the renal artery 12. The tip region (1) is defined between a distal tip of the slotted tube 230 and the turn region (3). The tip region (1) is configured to support the electrode(s) 208 and preferably has a curved shape. The tip region (1) preferably has a slot pattern configured to provide enhanced bending stiffness sufficient to maintain contact between the electrode(s) 208 and the wall 15 of the renal artery 12. In some embodiments, the multiplicity of regions defined along the length of the slotted tube 230 further includes an intermediate region (2) defined between the tip region (1) and the turn region (3). The slot pattern in the intermediate region (2) is preferably configured to provide a balance between torque transmission and bending flexibility. Not shown are transition regions between each of the distinct regions (1)-(4), which provide for a gradual change in slotted tube properties between regions.

FIG. 19 shows a representative RF renal therapy apparatus 300 in accordance with various embodiments of the disclosure. The apparatus 300 illustrated in FIG. 19 includes external electrode activation circuitry 320 which comprises power control circuitry 322 and timing control circuitry 324. The external electrode activation circuitry 320, which includes an RF generator, is coupled to temperature measuring circuitry 328 and may be coupled to an optional impedance sensor 326. The catheter 100, which can be configured as a guiding catheter, includes a shaft 202 that incorporates a lumen arrangement 211 configured for receiving an RF ablation wire configured as a slotted tube 230 and, if desired, a variety of other components, such as conductors, pharmacological agents, actuator elements, obturators, sensors, or other components as needed or desired. The catheter 100 is typically introduced into the arterial or venous system via a percutaneous access location 229.

The RF generator of the external electrode activation circuitry 320 may include a return pad electrode 330 that is configured to comfortably engage the patient's back or other portion of the body near the kidneys. Radiofrequency energy produced by the RF generator is coupled to the electrode 208 of the slotted tube 230 by conductor wires that extend between the electrode 208 and the proximal end of the catheter 100.

Renal denervation therapy using the apparatus shown in FIG. 19 is typically performed using the RF electrode 208 positioned at desired locations within the renal artery 12 and the return pad electrode 330 positioned on the patient's back, with the RF generator operating in a unipolar mode. In other implementations, two or more RF electrodes 208 can be situated at the distal end of the slotted tube 230 and configured for operation in a bipolar configuration, in which case the return electrode pad 330 is not needed. The radiofrequency energy flows through the electrode(s) 208 in accordance with a predetermined activation sequence (e.g., sequential or concurrent) and ablates target tissue which includes perivascular renal nerves.

In general, when renal artery tissue temperatures rise above about 113° F. (50° C.), protein is permanently damaged (including those of renal nerve fibers). If heated over about 65° C., collagen denatures and tissue shrinks. If heated over about 65° C. and up to 100° C., cell walls break and oil separates from water. Above about 100° C., tissue desiccates. According to some embodiments, the electrode activation circuitry 320 is configured to control activation and deactivation of the electrode(s) 208 in accordance with a predetermined energy delivery protocol and in response to signals received from temperature measuring circuitry 328. The electrode activation circuitry 320 preferably controls radiofrequency energy delivered to the electrode(s) 208 so as to maintain the current densities at a level sufficient to cause heating of the target tissue to at least a temperature of 55° C.

One or more temperature sensors situated at the distal end of the slotted tube 230 provide for continuous monitoring of renal artery tissue temperatures, and RF generator power is automatically adjusted so that the target temperatures are achieved and maintained. An impedance sensor arrangement 326 may be used to measure and monitor electrical impedance during RF denervation therapy, and the power and timing of the RF generator 320 may be moderated based on the impedance measurements or a combination of impedance and temperature measurements.

Marker bands 314 can be placed on one or multiple parts of the slotted tube 230 and the catheter's shaft 202 to enable visualization during the procedure. Other portions of the catheter's shaft 202, such as a hinge mechanism 356, may include a marker band 314. The marker bands 314 may be solid or split bands of platinum or other radiopaque metal, for example. Radiopaque materials are understood to be materials capable of producing a relatively bright image on a fluoroscopy screen or another imaging technique during a medical procedure. This relatively bright image aids the user in determining specific portions of the catheter 100 and slotted tube 230, such as the electrode 208, for example.

Various aspects of the disclosure embodiments can be applied to other directed energy mechanisms for renal nerve ablation, such as for directing laser or microwave or ultrasound or cryothermal energy or ionizing radiation to selected locations within the renal artery. “Back-up” support curves can be provided, akin to coronary guiding catheter curves, to use the opposite wall of the renal artery for additional support to ensure adequate contact between the electrode and the artery wall. These and other features disclosed in the following commonly owned patents and published applications can be selectively incorporated into the various embodiments disclosed herein:

U.S. Patent Publication No. 2011/0257523, filed as U.S. patent application Ser. No. 13/086,116 on Apr. 13, 2011, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/324,164 filed Apr. 14, 2010; U.S. Patent Publication No. 2011/0257641, filed as U.S. patent application Ser. No. 13/086,121 on Apr. 13, 2011, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/324,163 filed Apr. 14, 2010; U.S. Patent Publication No. 2012/0029496, filed as U.S. patent application Ser. No. 13/193,437 on Jul. 28, 2011, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/369,460 filed Jul. 30, 2010; U.S. Patent Publication No. 2011/0270238, filed as U.S. patent application Ser. No. 12/980,952 on Dec. 29, 2010, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/291,476 filed Dec. 31, 2009; U.S. Patent Publication No. 2011/0263921, filed as U.S. patent application Ser. No. 12/980,972 on Dec. 29, 2010, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/291,480 filed Dec. 31, 2009; U.S. Patent Publication No. 2011/0307034, filed as U.S. patent application Ser. No. 13/157,844 on Jun. 10, 2011, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/353,853 filed Jun. 11, 2010; and U.S. Patent Publication No. 2011/0264086, filed as U.S. patent application Ser. No. 13/087,163 on Oct. 14, 2011, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/324,165 filed Apr. 14, 2010, each of which is incorporated herein by reference.

Although many of the embodiments disclosed herein are directed to ablation of body tissue, it is to be understood that various embodiments are directed to control mechanisms situated at a distal end of an elongated flexible member that provide for precision movement of a component coupled to a distal end or other portion of the control mechanism, where the component need not include an ablation device. Embodiments of the disclosure are also directed to control mechanisms situated at a distal end of an elongated flexible member dimensioned for deployment within a vessel of the body that provide for precision movement of a component coupled to a distal end or other portion of the control mechanism. It is to be understood that even though numerous characteristics of various embodiments have been set forth in the foregoing description, together with details of the structure and function of various embodiments, this detailed description is illustrative only, and changes may be made in detail, especially in matters of structure and arrangements of parts illustrated by the various embodiments to the full extent indicated by the broad general meaning of the terms in which the appended claims are expressed. 

What is claimed is:
 1. An apparatus, comprising: a catheter comprising a flexible shaft having a proximal end, a distal end, a lumen extending between the ends, and a length; a flexible actuation member disposed within and moveable along the lumen and extendable between the proximal and distal ends of the shaft; a flexible support member at a distal end of the flexible actuation member and extendable beyond the distal end of the shaft; an electrode provided at a distal end of the flexible support member and configured to deliver RF energy to the renal nerve tissue; and a position converter provided at the distal end of the shaft and coupled between the distal end of the flexible actuation member and a proximal end of the flexible support member, the position converter configured to convert movement of the flexible actuation member into at least controlled rotational and axial movement of the electrode to one of a plurality of stable circumferential and axial positions.
 2. The apparatus of claim 1, wherein the position converter is disposed within the lumen of the flexible shaft; the flexible actuation member and the flexible support member define a continuous member; and the continuous member is movable within the position converter.
 3. The apparatus of claim 1, wherein the position converter is disposed within the lumen of the flexible shaft; and the flexible actuation member and the flexible support member define separate members.
 4. The apparatus of claim 1, wherein the position converter comprises a ratcheting arrangement configured to convert movement of the flexible actuation member into the at least controlled rotational movement of the electrode to one of the plurality of stable circumferential positions.
 5. The apparatus of claim 1, wherein the position converter comprises a ratcheting arrangement configured to convert movement of the flexible actuation member into the at least controlled axial movement of the electrode to one of the plurality of stable axial positions.
 6. The apparatus of claim 1, wherein the position converter comprises a ratcheting arrangement configured to convert movement of the flexible actuation member into the at least controlled axial and rotational movement of the electrode to one of the plurality of stable circumferential and axial positions.
 7. The apparatus of claim 6, wherein the ratcheting arrangement comprises a spring-loaded ratcheting element having a proximal end coupled to the distal end of the flexible actuation member and a distal end coupled to the proximal end of the flexible support member, the spring-loaded ratcheting element configured to align the electrode to one of the plurality of stable circumferential and axial positions.
 8. The apparatus of claim 6, wherein the ratcheting arrangement comprises: a spring-loaded ratcheting element having a proximal end coupled to the distal end of the flexible actuation member and a distal end coupled to the proximal end of the flexible support member; a plurality of spaced keyways each of which defines one of the plurality of stable axial and circumferential positions; and a key component provided at the distal end of the flexible support member and having a shape configured to be received by each of the keyways; wherein the ratcheting element aligns the key component of the flexible support member with one of the keyways and the electrode to one of the plurality of stable axial and circumferential positions.
 9. The apparatus of claim 1, wherein the position converter comprises a magnetic indexing arrangement configured to magnetically urge the electrode to one of the plurality of stable circumferential positions.
 10. The apparatus of claim 1, wherein the position converter comprises a magnetic indexing arrangement configured to magnetically urge the electrode to one of the plurality of stable circumferential positions and one of the plurality of stable axial positions.
 11. The apparatus of claim 10, wherein the magnetic indexing arrangement comprises: a magnet arrangement provided at the distal end of the shaft; and a magnet arrangement provided on the flexible actuation member, the magnet arrangements of the shaft and the flexible actuation member magnetically interacting to urge the electrode to one of the plurality of stable circumferential positions and one of the plurality of stable axial positions.
 12. The apparatus of claim 10, wherein the magnetic indexing arrangement comprises: a plurality of magnets provided at discrete circumferential and axial locations at the distal end of the shaft; and a plurality of magnets provided on the flexible actuation member at discrete axial locations of the flexible actuation member, the magnets of the shaft and the flexible actuation member magnetically interacting to selectably align the electrode to each of the plurality of stable circumferential and axial positions. 